Channel specific gain control including lateral suppression

ABSTRACT

A system is described for generating electrode stimulation signals for stimulation electrodes in an implanted electrode array on a given side of a bilateral cochlear implant system. A pre-processor module processes an acoustic audio signal with a bank of filters to generate a set of band pass signals each corresponding to a band of audio frequencies associated with one of the filters. An automatic gain control (AGC) circuit performs a channel specific dynamic amplitude mapping of the band pass signals to generate a set of compressed band pass signals. The AGC circuit uses a bilateral multiplication matrix characterizing a lateral suppression network and having at least one non-zero coupling element from a contralateral side. A stimulation timing module extracts stimulation information from the compressed band pass signals to generate stimulation timing signals. A pulse shaper module develops the stimulation timing signals into electrode stimulation signals to the stimulation electrodes.

This application is a continuation-in-part of U.S. patent applicationSer. No. 12/695,240, filed Jan. 28, 2010, which in turn claims priorityfrom U.S. Provisional Application 61/147,855, filed Jan. 28, 2009; allof which are incorporated herein by reference.

FIELD OF THE INVENTION

The present invention relates to medical implants, and more specificallyto signal processing for cochlear implant systems.

BACKGROUND ART

In a cochlear implant (CI) the amplitude of the acoustic audio signalhas to be mapped to a relatively small dynamic range which can bedelivered to the acoustic nerve. Typically two stages perform thisamplitude compression, a front-end automatic gain control (AGC) whichcontrols the overall loudness and an instantaneous non-linear mappingfunction of typically logarithmic shape which further compresses eachband-pass envelope. The dynamic AGC used in current CI systems usuallyapplies one gain to the entire analyzed frequency range before splittingthe acoustic audio signal into individual frequency bands. Such systemshave been shown to increase listening comfort and speech understandingin hearing aid (HA) users as well as CI users.

One possible drawback of such a system can occur in the presence of twosignals which are located in different frequency regions, such as aspeech signal in the presence of a continuous high frequency noise. Insuch an acoustic environment, the AGC gain would depend on the relativeamplitudes of the two signals. Assuming a loud high frequency noise, theAGC gain would be reduced by the noise signal which could result insuppression of the speech signal. In a unilaterally implanted patient,this might only result in reduced speech understanding. But inbilaterally implanted patients, there could also be a reduced ability tolocalize sound sources. For example, assuming the loud high frequencynoise source is located at the right side of the CI user, then theright-side AGC would reduce its gain more than the left-side AGC.Consequently, the interaural level differences at high frequencies wouldbe reduced, and since the acoustic head shadow effect is higher at highfrequencies, the interaural level difference at low frequency couldvanish or even be inverted. As a result, the low frequency components,for example originating from a car engine, would be perceived from thewrong side.

These undesirable side effects of front-end single channel signalcompression could generally be circumvented by using AGCs which compressindividual band pass signals instead of the broadband signal. Suchsolutions can be found both in hearing aids and in cochlear implantsystems. Speech understanding in the presence of noise sounds and soundlocalization in bilateral patients could potentially be enhanced. Onemajor drawback of such systems is the fact that spectral differencessuch as amplitude differences in adjacent analysis bands get reduced.Spectral information such as formant frequencies in speech signals couldalso be less accessible to HA and CI users.

There have been previous efforts to apply dynamic compression to bandpass signals. For example, FIG. 1 shows an arrangement described in U.S.Pat. No. 7,136,706 (incorporated herein by reference) which applies anoverall mapping to a pre-band pass signal and then band specificmapping. The pre-band pass mapping function is thought to be linear(i.e. a limiter). The post-band pass mapping function is implemented asa non-linear, compressive, or logarithmic transform. The inventors statethat the differences in acoustic spectrum component amplitudes aremaintained. By maintaining these differences, spectral smearing betweenchannels is reduced and speech cues are preserved. But dynamicadaptation of post-band pass compression would result in unwantedspectral smearing.

A second method which applies frequency specific gains is described inU.S. Pat. No. 6,731,767 (incorporated herein by reference). As shown inthe block diagram in FIG. 2, an acoustic audio signal is split into anumber of separate frequency bands and variable gain is applied to eachfrequency band independently. In contrast to previously used AGCcircuits, the gain is controlled by a gain comparator and statisticalestimates of each band pass signal are calculated and compared topredetermined hearing response parameters. Although the gain calculationappears to be dynamic in this patent, it does not describe anyinteraction between analysis channels.

U.S. Pat. No. 7,305,100 describes a dynamic compression process whichapplies channel specific gains for use in a hearing aid, although nomention is found of use in a cochlear implant system. Although as shownin FIG. 3, there is a gain control unit, no details are discussed withregards to interactions between the analysis frequency bands.

U.S. Patent Publication 2004/0136545 describes an arrangement fordistributed gain control which takes into account the interactionsbetween analysis channels. FIG. 4 shows a block diagram of thearrangement discussed which is described as providing a spectralenhancement system that includes distributed filters, energydistribution units, and a weighted-averaging unit. Instead of filterbanks as used in cochlear implants and hearing aids, a filter cascade isused with an energy-detector that is coupled to each filter and providesan energy-detection output signal. A weighted-averaging unit provides aweighted-averaging signal to each of the filters and distributed gain isapplied to the filter stages via a nonlinear function.

SUMMARY OF THE INVENTION

Embodiments of the present invention are directed to a system and methodfor generating electrode stimulation signals for stimulation electrodesin an implanted electrode array on a given side of a bilateral cochlearimplant system. A pre-processor module processes an acoustic audiosignal with a bank of filters to generate a set of band pass signalseach corresponding to a band of audio frequencies associated with one ofthe filters. An automatic gain control (AGC) circuit performs a channelspecific dynamic amplitude mapping of the band pass signals to generatea set of compressed band pass signals. The AGC circuit uses a bilateralmultiplication matrix characterizing a lateral suppression network andhaving at least one non-zero coupling element from a contralateral side.A stimulation timing module extracts stimulation information from thecompressed band pass signals to generate stimulation timing signals. Apulse shaper module develops the stimulation timing signals intoelectrode stimulation signals to the stimulation electrodes.

The AGC circuit may include a delay circuit that delays the amplitudemapping of the band pass signals by one or more samples and/or thatdownsamples the multiplication matrix. A gain calculation circuit mayapply an individual gain constant, which may be the same for all bandpass signals, or different for different band pass signals. The gaincalculation circuit may include an inverting functionality. A levelcompressor may perform a non-linear mapping of the lateral suppressionnetwork, for example using a non-linear MAP-law. The lateral suppressionnetwork may include interaural level differences.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows a typical prior art cochlear implant signal compressionarrangement.

FIG. 2 shows a prior art signal compression arrangement havingindependent channels.

FIG. 3 shows a prior art signal compression arrangement havingnon-interactive channel specific gains.

FIG. 4 shows a prior art signal compression system based on a filtercascade arrangement.

FIG. 5 shows a block diagram of a typical cochlear implant signalprocessing arrangement.

FIG. 6 shows a block diagram for a cochlear implant signal processingarrangement including channel specific volume control according to anembodiment of the present invention.

FIG. 7 shows further details of a channel specific volume controlarrangement with a lateral suppression network.

FIG. 8 shows functional details of an AGC arrangement.

FIG. 9 shows details of an AGC arrangement with lateral suppression.

DETAILED DESCRIPTION OF SPECIFIC EMBODIMENTS

Various embodiments of the present invention are directed to extendingcochlear implant signal processing with an additional signal processingblock that calculates channel specific dynamic amplitude mapping withgain suppression. Such an approach can enhance spectral details andmodel masking effects as known from normal hearing psychoacoustics. Inaddition, channel specific interaural level differences can be preservedin patients with bilateral cochlear implants.

FIG. 5 shows various function blocks in a typical cochlear implantsignal processing arrangement for generating electrode stimulationsignals for the stimulation electrodes in an implanted electrode array.A pre-processor module 501 initially pre-processes an acoustic audiosignal from a sensing microphone (e.g., by an initial AGC, a limiter,and/or noise reduction means) and then uses a filter bank to split theaudio signal into a set of band pass signals B_(n) where each band passsignal corresponds to a band of audio frequencies associated with one ofthe filters. A stimulation timing module 502 performs informationextraction and decimation to derive or determine a set of stimulationtiming signals A_(m) which in effect maps the filter analysis frequencybands to the stimulation electrodes. From these, a pulse shaper module503 performs an amplitude mapping and pulse shape definition to define aset of stimulation pulses E_(m) for the stimulation electrodes.

FIG. 6 shows functional blocks according to an embodiment of the presentinvention where an automatic gain control (AGC) module 601 uses alateral suppression network to perform channel specific dynamicamplitude mapping of the band pass signals to generate a set ofcompressed band pass signals S_(n) from the pre-processor module 501.The stimulation timing module 502 then derives the stimulation timingsignals A_(m) from the compressed band pass signals S_(n) and the pulseshaper module 503 produces the stimulation pulses E_(m).

FIG. 7 shows details of the additional signal processing block includingthe filter bank 701 and the coupling of the AGC modules 601 with alateral suppression network 702. FIG. 8 shows an example a typicalimplementation of an AGC module 601 with a signal multiplication node801 and four main components: a level detector 802, a level compressor803, a gain calculator 804, and delay module 804. Such AGC modules 601are typically used in front end compression and could generally also beused for channel specific compression, but the existing structure doesnot allow for lateral suppression and spectral enhancement. FIG. 9 showsan improved arrangement of the AGC module 601 where the signals O_(n)from the level detector 901 of all AGCs are routed to a lateralsuppression network and the level compressor 902 of each AGC is fed bythe output/return signal I_(n) of the lateral suppression network.

In a specific embodiment, the lateral suppression network 702 couldsimply apply a matrix multiplication as given in Equation 1:{right arrow over (I)}=W·{right arrow over (O)}  Equation 1where W is the matrix, and I and R the vectors containing all leveldetector and return signals, respectively. The unit matrix (Equation 2)results in individually acting AGCs:

$\begin{matrix}{W = \begin{pmatrix}1 & 0 & 0 & \ldots & \ldots & 0 & 0 & 0 \\0 & 1 & 0 & \ldots & \ldots & 0 & 0 & 0 \\0 & 0 & 1 & \ldots & \ldots & 0 & 0 & 0 \\\ldots & \ldots & \ldots & \ldots & \ldots & \ldots & \ldots & \ldots \\0 & 0 & 0 & \ldots & \ldots & 0 & 1 & 0 \\0 & 0 & 0 & \ldots & \ldots & 0 & 0 & 1\end{pmatrix}} & {{Equation}\mspace{14mu} 2}\end{matrix}$whereas Equation 3 shows a setup of the lateral suppression network 702,where level detector signals of three neighboring channels are averaged:

$\begin{matrix}{W = \begin{pmatrix}0.33 & 0.66 & 0 & \ldots & \ldots & 0 & 0 & 0 \\0.33 & 0.33 & 0.33 & \ldots & \ldots & 0 & 0 & 0 \\0 & 0 & 0 & \ldots & \ldots & 0 & 0 & 0 \\\ldots & \ldots & \ldots & \ldots & \ldots & \ldots & \ldots & \ldots \\0 & 0 & 0 & \ldots & \ldots & 0.33 & 0.33 & 0.33 \\0 & 0 & 0 & \ldots & \ldots & 0 & 0.66 & 0.33\end{pmatrix}} & {{Equation}\mspace{14mu} 3}\end{matrix}$A similar case with a subtle difference is shown in Equation 4 whereelements in the main diagonal of the matrix are smaller:

$\begin{matrix}{W = \begin{pmatrix}0.1 & 0.9 & 0 & \ldots & \ldots & 0 & 0 & 0 \\0.45 & 0.1 & 0.45 & \ldots & \ldots & 0 & 0 & 0 \\0 & 0.45 & 0.1 & \ldots & \ldots & 0 & 0 & 0 \\\ldots & \ldots & \ldots & \ldots & \ldots & \ldots & \ldots & \ldots \\0 & 0 & 0 & \ldots & \ldots & 0.45 & 0.1 & 0.45 \\0 & 0 & 0 & \ldots & \ldots & 0 & 0.9 & 0.1\end{pmatrix}} & {{Equation}\mspace{14mu} 4}\end{matrix}$In this case a channel containing smaller amplitude would be suppressedby a neighboring channel with higher amplitude. The main diagonal is setto zero in Equation 5:

$\begin{matrix}{W = \begin{pmatrix}0 & 0.5 & 0.25 & \ldots & \ldots & 0.01 & 0 & 0 \\0.33 & 0 & 0.33` & \ldots & \ldots & 0.01 & 0.01 & 0 \\0.14 & 0.29 & 0 & \ldots & \ldots & 0.02 & 0.01 & 0 \\\ldots & \ldots & \ldots & \ldots & \ldots & \ldots & \ldots & \ldots \\0 & 0.01 & 0.01 & \ldots & \ldots & 0.33 & 0 & 0.33 \\0 & 0 & 0.01 & \ldots & \ldots & 0.25 & 0.5 & 0\end{pmatrix}} & {{Equation}\mspace{14mu} 5}\end{matrix}$Additionally, all other elements decay exponentially. Decaycharacteristics can be different in the upper and lower triangularmatrix. The system allows individual adjustment of the range and form ofsuppression in terms of analysis bands. Numerical stability of thesystem can be provided by normalization of the matrix andapplication-specific constraints.

Laterally suppressed AGCs (as described above) allow simulation ofspectral masking and/or spectral sharpening effects as known from normalhearing. At the same time, distant channels can be configured to workindependently. Thus, the negative side effects (described in theBackground) of single channel AGC and simple independent channelspecific AGCs can be avoided. For example, a low frequency signal (e.g.speech) will no longer be suppressed by a louder high frequency signal(e.g., noise). And bilaterally implanted users would be able to morecorrectly identify directions of simultaneous spectrally separatedsignals. Spectral smearing as seen with entirely independent AGCs can beavoided and spectral differences can be enhanced for further signalprocessing stages. Besides laterally suppressed AGCs as described above,a weighting matrix can be used with a similar architecture to implementindependent AGCs or laterally averaged AGCs.

As recognized above, lateral suppression networks may be especiallyuseful in bilateral systems where there is an implanted electrode arrayin both the left and right ears. As explained above, the embodimentshown in FIG. 9 uses a lateral suppression network to perform channelspecific dynamic amplitude mapping of the set of band pass signals B_(n)to generate a set of compressed band pass signals S_(n). In specificarrangements, the band pass signals B_(n) may be envelope or band passsignals and the compressed band pass signals 5, may be envelope signals.

The band pass signals B_(n) are input to the AGC multiplier node 801which is coupled to the lateral suppression network using one or more ofa delay block (Z⁻¹) 805, a gain calculation block 804, a levelcompressor 902 and/or a level detector 901. The delay block 805 maydelay the lateral suppression signal by one or more samples so as toform a control circuit, and/or the delay block 805 may downsample thelateral suppression signal output from the gain calculation block 804which may also reflect an inverting functionality. The level compressor902 may specifically perform any non-linear mapping, for example, usinga non-linear MAP-law such as:log(1+C·l _(n))/log(1+C)  Equation 6The level compressor 902 multiplies the l_(n) signal from the lateralsuppression network 702 by an individual gain-constant C, increases byone, logarithmizes and scales. The gain constant C may be the same forall channels or different for each channel. In another embodiment thegain calculation block 804 may additionally down-sample the signal.Level detector 901 upsamples the compressed band pass signals S_(n)before they are input to the lateral suppression network 702 as outgoingsignals O_(n) that suppress short harsh acoustic signals. The leveldetector 901 also may calculate the loudness level of the compressedband pass signals S_(n). Due to the non-linear functions, it isnecessary to up-sample the compressed band pass signals S_(n) and runthe calculations of the lateral suppression network 702 at a higher ratethan the band pass signals themselves. Before multiplication by the AGCmultiplication node 801, the delay block 805 downsamples the signalsagain.

The lateral suppression network 702 may be a multiplication matrix thatreflects channel specific interaural level differences. Specifically,such a multiplication matrix may include the pre-processed signals O_(n)from the contralateral (opposite) side of the bilateral CI system.Herein is described the use of a dynamically updated multiplicationmatrix, but some embodiments may be based on a static multiplicationmatrix with matrix coefficients that are set during a patient fittingsession. The pre-processed signals O_(n) are calculated in the samemanner on both sides of the bilateral system and exchanged between thecochlear implant systems. Either directly or via a communication unit.It may be advantageous if the pre-processed signals O_(n) arecommunicated in only one direction at a time from one side to the otherof the bilateral CI system (e.g., based on the pre-processed signalsO_(n)) though the direction of communication may alternate. Thepre-processed signals O_(n) may be averaged, for example, by means of alow-pass filter and communicated only in the case where the differencefrom the previously communicated pre-processed signals O_(n) exceeds apre-determined threshold so that the amount of data to be exchanged andthe power consumption can be minimized. Such a communication thresholdmay depend on the listening scenario, e.g., in case of a loudenvironment and in case of a quiet environment.

The lateral suppression network 702 multiplication matrix W may beextended by the channels from the contra-lateral side. For example, L1 .. . L4 represents four channels from the left side cochlear implantsystem and R1 . . . R4 from the right side cochlear implant system. Thenew bilateral matrix W_(bi) may be expressed by

$\begin{matrix}{W_{bi}\begin{pmatrix}W_{L} & W_{L - R} \\W_{R - L} & W_{R}\end{pmatrix}} & {{Equation}\mspace{14mu} 7}\end{matrix}$Where W_(L) and W_(R) are the sub-matrices for the left and right sidedcochlear implant systems respectively. Both sub-matrices are defined inthe same way as matrix W of Equation 1. The W_(L-R) and W_(R-L)sub-matrices are the coupling matrices for the left sided cochlearimplant system from the contralateral right sided system and vice-versarespectively, for example:

$\begin{matrix}{W_{bi} = \begin{pmatrix}0.5 & 0.25 & 0 & 0 & 0 & 0 & 0 & 0 \\0.25 & 0.5 & 0.25 & 0 & 0 & 0 & 0 & 0 \\0 & 0.25 & 0.5 & 0.25 & 0 & 0 & 0 & 0 \\0 & 0 & 0.25 & 0.5 & 0 & 0 & 0 & 0 \\0 & 0 & 0 & 0 & 0.5 & 0.25 & 0 & 0 \\0 & 0 & 0 & 0 & 0.25 & 0.5 & 0.25 & 0 \\0 & 0 & 0 & 0 & 0 & 0.25 & 0.5 & 0.25 \\0 & 0 & 0 & 0 & 0 & 0 & 0.25 & 0.5\end{pmatrix}} & {{Equation}\mspace{14mu} 8}\end{matrix}$In the example shown in Equation 8, the left and right side CI systemsdo not distribute their level/energy from the contralateral side and theupper right and lower left 4×4 sub-matrices of the matrix are zero. Inthis case, the bilateral matrix W_(bi) will map in the exact same way asmatrix W does (Equ. 1 of application).

The example of the bilateral matrix W_(bi) shown in Equation 9 doescouple the left and right side CI systems:

$\begin{matrix}{W_{bi} = \begin{pmatrix}1 & 0 & 0 & 0 & 0.2 & 0 & 0 & 0 \\0 & 1 & 0 & 0 & 0 & 0.2 & 0 & 0 \\0 & 0 & 1 & 0 & 0 & 0 & 0.2 & 0 \\0 & 0 & 0 & 1 & 0 & 0 & 0 & 0.2 \\0.2 & 0 & 0 & 0 & 1 & 0 & 0 & 0 \\0 & 0.2 & 0 & 0 & 0 & 1 & 0 & 0 \\0 & 0 & 0.2 & 0 & 0 & 0 & 1 & 0 \\0 & 0 & 0 & 0.2 & 0 & 0 & 0 & 1\end{pmatrix}} & {{Equation}\mspace{14mu} 9}\end{matrix}$The upper right and lower left 4×4 sub-matrices have non-zerocoefficients. In Equation 9, the left and right side CI systems arecoupled, but there is no lateral suppression from adjacent channels. Forexample channel L2 suppresses channel R1.

The bilateral matrix W_(bi) shown in Equation 10 does have both couplingof the left and right side CI systems and lateral suppression fromadjacent channels:

$\begin{matrix}{W_{bi} = \begin{pmatrix}0.5 & 0.25 & 0 & 0 & 0.2 & 0 & 0 & 0 \\0.25 & 0.5 & 0.25 & 0 & 0.2 & 0 & 0 & 0 \\0 & 0.25 & 0.5 & 0.25 & 0 & 0.2 & 0 & 0 \\0 & 0 & 0.25 & {0.;5} & 0 & 0 & 0.2 & 0 \\0.2 & 0 & 0 & 0 & 0.5 & 0.25 & 0 & 0 \\0.2 & 0 & 0 & 0 & 0.25 & 0.5 & 0.25 & 0 \\0 & 0.2 & 0 & 0 & 0 & 0.25 & 0.5 & 0.25 \\0 & 0 & 0.2 & 0 & 0 & 0 & 0.25 & 0.5\end{pmatrix}} & {{Equation}\mspace{14mu} 10}\end{matrix}$

Embodiments of the invention may be implemented in whole or in part anyconventional computer programming language. For example, preferredembodiments may be implemented in a procedural programming language(e.g., “C”) or an object oriented programming language (e.g., “C++”,Python). Alternative embodiments of the invention may be implemented aspre-programmed hardware elements, other related components, or as acombination of hardware and software components.

Embodiments can be implemented in whole or in part as a computer programproduct for use with a computer system. Such implementation may includea series of computer instructions fixed either on a tangible medium,such as a computer readable medium (e.g., a diskette, CD-ROM, ROM, orfixed disk) or transmittable to a computer system, via a modem or otherinterface device, such as a communications adapter connected to anetwork over a medium. The medium may be either a tangible medium (e.g.,optical or analog communications lines) or a medium implemented withwireless techniques (e.g., microwave, infrared or other transmissiontechniques). The series of computer instructions embodies all or part ofthe functionality previously described herein with respect to thesystem. Those skilled in the art should appreciate that such computerinstructions can be written in a number of programming languages for usewith many computer architectures or operating systems. Furthermore, suchinstructions may be stored in any memory device, such as semiconductor,magnetic, optical or other memory devices, and may be transmitted usingany communications technology, such as optical, infrared, microwave, orother transmission technologies. It is expected that such a computerprogram product may be distributed as a removable medium withaccompanying printed or electronic documentation (e.g., shrink wrappedsoftware), preloaded with a computer system (e.g., on system ROM orfixed disk), or distributed from a server or electronic bulletin boardover the network (e.g., the Internet or World Wide Web). Of course, someembodiments of the invention may be implemented as a combination of bothsoftware (e.g., a computer program product) and hardware. Still otherembodiments of the invention are implemented as entirely hardware, orentirely software (e.g., a computer program product).

Although various exemplary embodiments of the invention have beendisclosed, it should be apparent to those skilled in the art thatvarious changes and modifications can be made which will achieve some ofthe advantages of the invention without departing from the true scope ofthe invention.

What is claimed is:
 1. A system for generating electrode stimulationsignals for a plurality of stimulation electrodes in an implantedelectrode array on a given side of a bilateral cochlear implant systemhaving an implanted electrode array in each ear of an implanted patient,the system comprising: a pre-processor module configured for processingan acoustic audio signal with a bank of filters to generate a set ofband pass signals, each band pass signal corresponding to a band ofaudio frequencies associated with one of the filters; an automatic gaincontrol (AGC) circuit configured for performing a channel specificdynamic amplitude mapping of the band pass signals to generate a set ofcompressed band pass signals, the AGC circuit using a bilateralmultiplication matrix characterizing a lateral suppression network andhaving at least one non-zero coupling element from a contralateral side;a stimulation timing module configured for extracting stimulationinformation from the compressed band pass signals to generate a set ofstimulation timing signals; and a pulse shaper module configured fordeveloping the stimulation timing signals into a set of electrodestimulation signals to the stimulation electrodes.
 2. The systemaccording to claim 1, wherein the AGC circuit includes a delay circuitthat delays the amplitude mapping of the band pass signals by one ormore samples.
 3. The system according to claim 2, wherein the delaycircuit downsamples the multiplication matrix.
 4. The system accordingto claim 1, wherein the AGC circuit includes a gain calculation circuitthat applies an individual gain constant.
 5. The system according toclaim 4, wherein the gain constant is the same for all band passsignals.
 6. The system according to claim 4, wherein the gain constantis different for different band pass signals.
 7. The system according toclaim 4, wherein the gain calculation circuit includes an invertingfunctionality.
 8. The system according to claim 1, wherein the AGCcircuit includes a level compressor that performs a non-linear mappingof the lateral suppression network.
 9. The system according to claim 8,wherein the non-linear mapping reflects a non-linear MAP-law.
 10. Thesystem according to claim 1, wherein the lateral suppression networkincludes interaural level differences.
 11. A method of generatingelectrode stimulation signals for a plurality of stimulation electrodesin an implanted electrode array on a given side of a bilateral cochlearimplant system having an implanted electrode array in each ear of animplanted patient, the method comprising: for the stimulation electrodesof the implanted electrode array on the given side: i. processing anacoustic audio signal with a bank of filters to generate a set of bandpass signals, each band pass signal corresponding to a band of audiofrequencies associated with one of the filters; ii. performing a channelspecific dynamic amplitude mapping of the band pass signals to generatea set of compressed band pass signals using a bilateral multiplicationmatrix characterizing a lateral suppression network and having at leastone non-zero coupling element from a contralateral side; iii. extractingstimulation information from the compressed band pass signals togenerate a set of stimulation timing signals; and iv. developing thestimulation timing signals into a set of electrode stimulation signalsto the stimulation electrodes.
 12. The method according to claim 11,wherein the performing the channel specific dynamic amplitude mappingincludes delaying the amplitude mapping of the band pass signals by oneor more samples.
 13. The method according to claim 12, wherein thedelaying includes downsampling the multiplication matrix.
 14. The methodaccording to claim 11, wherein an individual gain constant is applied tothe multiplication matrix.
 15. The method according to claim 14, whereinthe gain constant is the same for all band pass signals.
 16. The methodaccording to claim 14, wherein the gain constant is different fordifferent band pass signals.
 17. The method according to claim 14,wherein an inverting functionality is applied with the gain constant.18. The method according to claim 11, wherein the multiplication matrixreflects a non-linear mapping of the lateral suppression network. 19.The method according to claim 18, wherein the non-linear mappingincludes a non-linear MAP-law.
 20. The method according to claim 11,wherein the lateral suppression network includes interaural leveldifferences.